Methods for using high intensity focused ultrasound and associated systems and devices

ABSTRACT

A plurality of concepts related to HIFU therapy are disclosed, including a technique to spatially track and display the relative positions of a HIFU focal point and an imaging plane from an ultrasound imager, so that a clinician can ensure that the HIFU focus remains in the image plane during HIFU therapy, thereby facilitating image guided HIFU therapy. Also disclosed are a plurality of transvaginal probes that include a HIFU transducer optimized for the treatment of uterine fibroids. In one embodiment, the probe includes a piezoceramic crystal bonded to an aluminum lens, to achieve a HIFU transducer having a focal length of about 4 cm. In another embodiment, the probe includes a generally spoon-shaped transducer including a plurality of individual emitter elements. Still another concept disclosed herein is a method for evaluating a quality of a coupling between a liquid-filled volume encompassing a HIFU transducer and a tissue interface.

RELATED APPLICATIONS

This application is a divisional of a patent application Ser. No.11/928,667, filed on Oct. 30, 2007, which itself is a divisional of apatent application Ser. No. 10/977,339, filed on Oct. 29, 2004, and nowissued as U.S. Pat. No. 7,520,856, the benefit of the filing date ofwhich is hereby claimed under 35 U.S.C. §120. Parent application Ser.No. 10/977,339 is based on a prior provisional application Ser. No.60/516,099, filed on Oct. 31, 2003, the benefit of the filing date ofwhich is hereby claimed under 35 U.S.C. §119(e). Further, parentapplication Ser. No. 10/977,339 is a continuation-in-part application ofprior application Ser. No. 10/770,350, filed on Feb. 2, 2004, and nowissued as U.S. Pat. No. 7,686,763, which itself is acontinuation-in-part application of prior application Ser. No.10/166,795, filed on Jun. 7, 2002 and now issued as U.S. Pat. No.6,716,184, which itself is a divisional application of prior applicationSer. No. 09/397,471, filed on Sep. 17, 1999 and now issued as U.S. Pat.No. 6,425,867, the benefit of the filing dates of which is herebyclaimed under 35 U.S.C. §120.

GOVERNMENT RIGHTS

This invention was made with U.S. government support under Grant No.N00014-01-96-0630 and N00014-01-G-0460 awarded by the Department of theNavy and grant number 2 R42 HD38440-02 awarded by National Institutes ofHealth. The U.S. government has certain rights in this invention.

BACKGROUND

High intensity focused ultrasound (HIFU) has emerged as a precise,non-surgical, minimally-invasive treatment for benign and malignanttumors. At focal intensities (1000-10000 W/cm²) that are 4-5 orders ofmagnitude greater than that of diagnostic ultrasound (approximately 0.1W/cm²), HIFU can induce lesions (i.e., localized tissue necrosis) at asmall, well defined region deep within tissue, while leaving interveningtissue between the HIFU transducer and the focal point substantiallyunharmed. Tissue necrosis is a result of tissue at the focal point ofthe HIFU beam being heated to over 70° C. in a very short period of time(generally less than one second). Tissue necrosis also results fromcavitation activity, which causes tissue and cellular disorganization.HIFU is currently being used clinically for the treatment of prostatecancer and benign prostatic hyperplasia, as well as the treatment ofmalignant bone tumors and soft tissue sarcomas. Clinical trials arecurrently being conducted for HIFU treatment of breast fibroadenomas,and various stage-4 primary and metastatic cancerous tumors of thekidney and liver.

Uterine fibroids are benign tumors of the uterus that cause abnormaluterine bleeding. The incidence of fibroids in women in theirreproductive years has been estimated to be 20-25%, although autopsystudies show an incidence to be greater than 75%. Approximately ⅓ ofwomen experiencing uterine fibroids will have a tumor that issymptomatic requiring treatment. Approximately 30% of all hysterectomiesare related to the presence of uterine fibroids. Current treatmentmethods for uterine fibroids include both drug therapy and surgery.Experience with drug therapy shows almost a 100% rate of tumorreoccurrence once the drug therapy has stopped, and the drug therapy hasnumerous undesirable side effects. The rate of reoccurrence issignificantly less for the surgical therapy (about 15%). Unfortunately,most current procedures for removing uterine fibroids are based oninvasive surgical techniques, which require a significant recoveryperiod and involve significant risks (such as blood loss, damage torelated organs, and the ever present risk of infection). It is estimatedthat uterine fibroid procedures in the United States alone account for1.2 to 3.6 billion dollars in annual medical costs.

It appears that HIFU, delivered using a transvaginal transducer, couldprovide a minimally-invasive treatment for uterine fibroids. On Oct. 22,2004, the United States Food and Drug Administration (FDA) approved theExAblate 2000™ System; a new medical device that uses magnetic resonanceimage (MRI) guided focused ultrasound to target and destroy uterinefibroids. While MRI guided HIFU therapy offers an alternative to moreinvasive surgical techniques, MRI equipment is very expensive, notnearly as available as ultrasound imaging devices, and not nearly asportable as ultrasound imaging devices. It would be desirable to providea less costly alternative to MRI guided HIFU therapy. Such treatment isexpected to compare favorably with the costs for the current drugrelated therapy for the treatment of uterine fibroids and its efficacyshould compare favorably with the higher success rate of the currentsurgical procedures, but without the attendant risks. It would furtherbe desirable to provide additional techniques and tools to enhance HIFUtherapy.

SUMMARY

A first aspect of the concepts disclosed herein is directed to methodand apparatus configured to spatially track and display the relativepositions of a HIFU focal point and an imaging plane from an ultrasoundimager, so that a clinician can ensure that the HIFU focus remains inthe image plane during HIFU therapy, thereby facilitating image guidedHIFU therapy.

Another aspect of the concepts disclosed herein is directed to atransvaginal probe that includes a HIFU transducer optimized for thetreatment of uterine fibroids from within the vagina. In one embodiment,the transvaginal probe includes a piezoceramic crystal bonded to analuminum lens, to achieve a HIFU transducer having a focal length ofabout 4 cm. In another embodiment, the transvaginal probe includes agenerally spoon-shaped transducer, which comprises a plurality ofindividual emitter elements.

Still another aspect of the concepts disclosed herein is a method forevaluating a quality of a coupling between a liquid-filled volumeencompassing a HIFU transducer and a tissue interface. HIFU transducers,or a portion of a probe containing a HIFU transducer, are often disposedinside a liquid-filled membrane. The fluid helps enhance the propagationof the HIFU beam by coupling the beam into the adjacent tissue. If anyair bubbles are present between the liquid-filled membrane and thetissue interface, they will negatively affect the HIFU treatment byreducing the power of the HIFU transferred to the tissue. In a firstembodiment, a hysterscopei is used to visually detect the presence ofsuch bubbles. The hysterscope can be a separate instrument, or can beintegrated into the HIFU probe. In a second embodiment, the HIFUtransducer is first energized at a lower power setting. If any airbubbles are present in the tissue interface, a portion of the low powerbeam emitted from the HIFU transducer will be reflected. Suchreflections are detected, and if the amount of reflected energy isgreater than a threshold value, specific steps will be taken to dislodgethe air bubbles. In a third embodiment, an imaging probe is used toimage the therapy probe/tissue interface. Any air bubbles that arepresent in this interface will show up as a bright spot in theultrasound image. If such bright spots are identified, proper steps aretaken to dislodge the air bubbles. Techniques for dislodging air bubblesinclude repositioning the therapy probe to dislodge the air bubbles,inflating or deflating the liquid-filled membrane to dislodge the airbubbles, and flushing the interface with an irrigation liquid todislodge the air bubbles.

Apparatus for implementing the above identified method is also disclosedherein.

This Summary has been provided to introduce a few concepts in asimplified form that are further described in detail below in theDescription. However, this Summary is not intended to identify key oressential features of the claimed subject matter, nor is it intended tobe used as an aid in determining the scope of the claimed subjectmatter.

DRAWINGS

Various aspects and attendant advantages of one or more exemplaryembodiments and modifications thereto will become more readilyappreciated as the same becomes better understood by reference to thefollowing detailed description, when taken in conjunction with theaccompanying drawings, wherein:

FIG. 1A (prior art) schematically illustrates an ultrasonic imagegenerated during the simultaneous use of ultrasound for imaging and forproviding HIFU therapy in a conventional manner, wherein noise due tothe HIFU beam obscures the entire image;

FIG. 1B schematically illustrates an ultrasonic image generated duringthe simultaneous use of ultrasound for imaging and therapy, whereinpulsing of the HIFU limits the resulting noise to a portion of theimage;

FIG. 1C schematically illustrates an ultrasonic image generated duringthe simultaneous use of ultrasound for imaging and therapy, whereinsynchronized pulsing of the HIFU is used to shift the noise caused bythe HIFU beam away from a treatment site displayed in the image;

FIG. 2 is a schematic view of a vaginal therapy probe that includes atherapeutic HIFU transducer and a transabdominal imaging probe beingused for the simultaneous imaging and treatment of a tumor in a femalereproductive system;

FIG. 3 is a block diagram schematically illustrating the elements of asystem for use with the present invention to facilitate free handvisualization of the focal point of a HIFU beam during therapy;

FIG. 4 schematically illustrates an exemplary image provided by thesystem of FIG. 3, enabling a clinician to determine how to manipulate aspatial relationship between an imaging probe and a therapy probe toensure visualization of the focal point of a HIFU beam during therapy(noting that different treatment sites are being shown in the differentFigures);

FIG. 5 schematically illustrates a distal end of an exemplarytransvaginal HIFU therapy probe including an aluminum lens;

FIG. 6 schematically illustrates an internal view of part of thetransvaginal HIFU therapy probe of FIG. 5;

FIGS. 7A-7F illustrate elements used to assemble a working embodiment ofthe transvaginal HIFU therapy probe of FIG. 5;

FIGS. 8A and 8B are ultrasound images illustrating how noise generatedby the HIFU beam can be shifted to a portion of the ultrasound imagethat avoids interference with a visualization of the focal point of theHIFU beam during therapy;

FIG. 9 is a block diagram schematically illustrating the elements of asystem for use with the present invention to facilitate visualization ofthe focal point of a HIFU beam during therapy;

FIGS. 10A and 10B graphically illustrate preferred geometries of theHIFU transducer and lens employed in the transvaginal HIFU therapy probeof FIG. 5;

FIG. 11A is a composite of images extracted from a computer simulationused to design the HIFU transducer for use in the transvaginal therapyprobe of FIG. 5;

FIG. 11B graphically illustrates peak normalized particle displacementscollected from the computer simulation used to design the HIFUtransducer for use in the transvaginal therapy probe of FIG. 5,indicating estimated focal dimensions of 10 mm in length by 1 mm inwidth;

FIG. 12A is a composite of Schlieren images obtained during empiricaltesting of the HIFU transducer used in the transvaginal therapy probe ofFIG. 5;

FIG. 12B graphically illustrates an acoustic field map created usingdata collected with a PVDF needle hydrophone during empirical testing ofthe HIFU transducer designed for use in the transvaginal therapy probeof FIG. 5, indicating focal point dimensions of 11 mm in length and 1.2mm in width;

FIG. 13 graphically illustrates the correlation between electrical powerand acoustic power for the HIFU transducer used in the transvaginaltherapy probe of FIG. 5;

FIG. 14A is a composite image including both a photograph of the distalend of the transvaginal therapy probe of FIG. 5 coupled to a gel phantomand an ultrasound image of the distal end of transvaginal therapy probeof FIG. 5 coupled to the gel phantom;

FIG. 14B is a composite image including both a photograph and ultrasoundimage, substantially similar to those of FIG. 14A, after the applicationof HIFU therapy, wherein a lesion is visible in both the photograph andthe ultrasound image;

FIG. 15A is a photograph of a turkey breast including a plurality oflesions formed using a HIFU beam generated with the transvaginal probeof FIG. 5;

FIG. 15B is a composite image including before and after ultrasoundimages showing the transvaginal probe of FIG. 5 being positioned toapply HIFU therapy to a turkey breast, wherein a lesion is visible inthe after image;

FIG. 16 is a flowchart illustrating the logical steps implemented in amethod for determining whether any air bubbles are present at aninterface between a therapy probe and a mass of tissue, in accord withanother aspect of the present invention;

FIG. 17A schematically illustrates a transvaginal therapy probe beingcoupled to a mass of tissue, so that a plurality of air bubbles aretrapped at the tissue interface;

FIG. 17B schematically illustrates a transvaginal therapy probe beingcoupled to a mass of tissue, such that no air bubbles are trapped at thetissue interface;

FIG. 18 is a photograph of a prior art hysterscope that is useful tooptically determine whether any air bubbles are present at the tissueinterface;

FIG. 19A schematically illustrates a second embodiment of a transvaginaltherapy probe in accord with the present invention;

FIG. 19B schematically illustrates a generally spoon shaped transducerof the transvaginal therapy probe shown in FIG. 19A;

FIG. 19C schematically illustrates the transvaginal therapy probe ofFIG. 19A removably coupled to a prior art imaging probe and hysterscope,indicating how each instrument is used during a therapeutic procedure;and

FIG. 19D schematically illustrates a plurality of emitter elementscomprising the HIFU transducer in the transvaginal therapy probe ofFIGS. 19A-C.

DESCRIPTION Figures and Disclosed Embodiments are not Limiting

Exemplary embodiments are illustrated in referenced Figures of thedrawings. It is intended that the embodiments and Figures disclosedherein are to be considered illustrative rather than restrictive. Nolimitation on the scope of the technology and of the claims that followis to be imputed to the examples shown in the drawings and discussedherein.

The terms “therapeutic transducer,” “HIFU transducer,” and “highintensity transducer,” as used herein and in the claims that follow allrefer to a transducer that is capable of being energized to produceultrasonic waves that are much more energetic than the ultrasonic pulsesproduced by an imaging transducer, and which can be focused or directedonto a discrete location, such as a treatment site in a target area.However, in at least one embodiment of the present invention, not allultrasonic waves produced by such a transducer are necessarily at a highintensity, as is explained below.

When administering HIFU therapy, it is very desirable to be able toobserve a treatment site, to ensure that lesions induced by the HIFUtherapy are being produced at the desired location. Failure to properlyaim the HIFU beam will result in undesired tissue necrosis of non targettissue. From a practical standpoint, this goal has not proven easy toaccomplish when ultrasound is used to visualize the focal point, becausethe HIFU beam used for therapy completely saturates the signal providedby the imaging transducer. One analogy that might help to make thisproblem clear relates to the relative intensities of light. Consider thelight coming from a star in the evening sky to be equivalent to the lowpower imaging ultrasound waves that are reflected from a target areatoward the imaging transducer, while the light from the sun isequivalent to the HIFU generated by the therapy transducer. When the sunis out, the light from the stars is completely overwhelmed by the lightfrom the sun, and a person looking into the sky is unable to see anystars, because the bright light from the sun makes the dim light comingfrom the stars substantially imperceptible. Similarly, the HIFU emittedby the therapy transducer completely overwhelms the ultrasonic wavesproduced by the imaging transducer, and any ultrasonic image generatedis completely saturated with noise caused by the HIFU emitted from thetherapeutic transducer.

FIG. 1A illustrates an ultrasound image 10 in which a scanned imagefield 12 is completely obscured by noise 14, as is typical during thesimultaneous reception of energy from a reflected imaging pulse and aHIFU wave (neither shown). In regard to ultrasound image 10, a clinicianmay desire to focus the HIFU wave on a treatment site 18. However,because noise 14 completely saturates scanned image field 12, it isvirtually impossible to accurately focus the HIFU wave onto treatmentsite 18. If the therapy transducer is completely de-energized, noise 14is eliminated from the scanned image field. However, under theseconditions, the focal point of the HIFU wave will not be seen, and thus,the HIFU wave cannot be accurately focused on treatment site 18. Whilesome change in echogenicity at the HIFU focal point will persist for atime after the HIFU wave is no longer present, any change in a positionof the therapy transducer (or treatment site 18) will not register untilthe therapeutic transducer is re-energized, and thus, the HIFU wavecannot be focused in real time.

Some prior art systems have included a targeting icon in an ultrasoundimage to indicate the position of the known focal point of a specificHIFU transducer in a scanned image. While this icon may be helpful indetermining whether the HIFU was previously focused, it still does notenable a clinician to observe real-time results. Once the HIFUtherapeutic transducer is energized, the scanned ultrasound image iscompletely saturated with noise, and the clinician cannot monitor theprogress of the treatment without again de-energizing the HIFUtherapeutic transducer.

FIG. 1B illustrates one technique in which the effect of noisedisrupting the ultrasound image is reduced. In FIG. 1B, the HIFU wavegenerated by the therapeutic transducer has been pulsed. This techniqueproduces an ultrasound image 20, in which the location of noise 24 in ascanned field 22 is a function of the interference between the pulsedHIFU wave generated by the therapy transducer and the ultrasonic imagingultrasound pulses generated by the scanning transducer. In FIG. 1B,noise 24 substantially masks a treatment site 28. This result will notoccur in all cases, because to an observer, noise 24 will move acrossscanned filed 22 as the interference between the HIFU waves and theimaging pulses varies in time. Pulsing of the HIFU wave alone can thusenable the clinician to view a noise-free image of the treatment siteonly when noise 24 is randomly shifted to a different part of scannedfield 22, away from the treatment site. However, this pulsing of theHIFU beam generates an image that is extremely distracting to aclinician, as noise 24 flickers across scanned field 22, making itdifficult to concentrate and difficult to consistently determine wherethe focal point of the HIFU wave is relative to the treatment site, inreal time.

FIG. 1C illustrates an ultrasound image 30 in which a HIFU wave from atherapy transducer has been both pulsed and synchronized with respect tothe ultrasonic imaging pulses from an imaging transducer, to ensure thatnoise 34 does not obscure a treatment site 38. In ultrasound image 30,noise 34 has been shifted to a location within a scanned field 32 of theimage that is spaced apart from treatment site 38, by selectivelyadjusting both the pulsing and the synchronization of the HIFU waverelative to the image pulses. Preferably, noise 34 is shifted completelyaway from treatment site 38, enabling the clinician to view anoise-free, stable image of treatment site 38 that clearly shows thelocation of the focal point of the HIFU wave relative to the treatmentsite. Thus, the HIFU wave can be focused in real time onto treatmentsite 38, and a clinician can, in real time, view the therapeutic effectsof the HIFU wave on treatment site 38. It will therefore be apparentthat a clinician can de-energize the therapeutic transducer, terminatingthe generation of the HIFU wave as soon as a desired therapeutic effecthas been achieved at the treatment site. In this manner, undesiredeffects on non target tissue can be minimized.

While combination imaging and therapy probes can be employed to achieveimage guided HIFU therapy, many medical offices have access totransabdominal imaging probes. Thus, one aspect of the conceptsdisclosed herein is directed to using the relatively ubiquitoustransabdominal ultrasound imaging probes with a transvaginal HIFU probeto achieve simultaneous imaging and administration of HIFU therapy for atreatment site. In FIG. 2, a HIFU transducer 102 a is included on avaginal probe 109, and an imaging transducer 104 a is part of atransabdominal probe 104. Vaginal probe 109 has been inserted into avaginal canal 108 a and positioned to enable imaging transducer 104 a oftransabdominal probe 104 to be used in generating an ultrasonic image ofa tumor 110 a. Once tumor 110 a has been located, HIFU transducer 102 ais focused on a selected portion of tumor 110 a to which the cliniciandesires to administer the HIFU therapy to generate a lesion 112 a. TheHIFU therapy is used to destroy the tumor by causing lesions of theblood vessels supplying oxygen and nutrients to the tumor, therebygenerating a plurality of lesions similar to lesion 112 a, so that thetumor withers away, or by destroying spaced-apart portions of the tumor.Particularly if the latter technique is used, the HIFU therapy willlikely be repeated at intervals of several weeks. The time betweensuccessive therapy sessions enables macrophages in the patient's body toclear away or debride the necrotic tissue from the tumor so that it isreduced in size with each therapy session and is eventually destroyed.

It must be recognized that because HIFU transducer 102 a and imagingtransducer 104 a are not both disposed on vaginal probe 109, maintainingthe required spatial orientation between HIFU transducer 102 a andimaging transducer 104 a, such that the focal point of the HIFU beamprovided by HIFU transducer 102 a lies within the imaging plane providedby imaging transducer 104 a, can be problematic. Once transabdominalprobe 104 and vaginal probe 109 are properly positioned, if either probe(or the patient) changes position, the spatial orientation orrelationship between the therapy and imaging probes may be changed, suchthat the focal point of the HIFU beam may no longer lie within theimaging plane provided by the imaging transducer. Clearly, such movementcan undesirably result in the inability to monitor the effects of theHIFU therapy being administered, in real time.

Thus one aspect of the concepts disclosed herein is a system and methodthat enables free hand registration of the imaging and therapy probes.FIG. 3 schematically illustrates a system 450 that facilitates such freehand registration. System 450 includes a HIFU therapy probe 452, anultrasound imaging probe 456, a tracking system 454, and a display 460.It should be understood that any type of HIFU therapy probe (configuredfor internal or external use), and any type of ultrasound imaging probe(configured for internal or external use), can be used in conjunctionwith system 450. Instead of using a physical or mechanical frame tomaintain a spatial relationship between the HIFU therapy probe and theultrasound imaging probe, system 450 relies on tracking system 454 toensure that the spatial relationship between the HIFU therapy probe andthe ultrasound imaging probe enables the focal point of the HIFU therapyprobe to be visualized in the imaging plane generated by the ultrasoundimaging probe. Tracking system 454 includes a processor that is able tokeep track of the spatial relationship between the ultrasound imagingprobe and the HIFU therapy probe. Such tracking systems are commerciallyavailable, and can be obtained from companies such as AscensionTechnology, of Milton, Vt. Tracking systems for medical instruments areavailable based on several different technologies, including acoustic,light and magnetic based tracking systems, any of which could be used toimplement tracking system 454. Magnetic based tracking systems(Ascension PC BIRD) that could be used for medical instruments areavailable from Mind Flux of Roseville, Australia.

System 450 functions as follows. HIFU therapy probe 452 and ultrasoundimaging probe 456 are positioned relative to patient 458. The cliniciancan view an image 462 on a display 460. Image 462 includes arepresentation of patient 458, and the relative locations of ultrasoundimaging probe 456 and HIFU therapy probe 452. Preferably image 462 willinclude a visual representation of the imaging plane provided byultrasound imaging probe 456, and the HIFU beam generated by HIFUtherapy probe 452. The clinician can determine from image 462 whether ornot ultrasound imaging probe 456 and HIFU therapy probe 452 are properlyaligned, such that the focal point of the HIFU beam can be visualized inan image provided by the ultrasound imaging probe. If the probes are notproperly aligned, image 462 will provide the clinician a reference fordetermining how to reposition one or more of ultrasound imaging probe456 and HIFU therapy probe 452, so that the focal point of the HIFU beamcan be visualized in the ultrasound image. Depending on the size ofdisplay 460, the ultrasound image provided by ultrasound imaging probe456 can be displayed along with image 462, or a separate display can beprovided to display the ultrasound image generated by ultrasound imagingprobe 456.

FIG. 4 is an enlarged view of display 460, including an image 463 (notea different treatment site is shown in FIG. 4 as compared to FIG. 3).The relative positions of ultrasound imaging probe 456, patient 458, andHIFU therapy probe 452 are presented in image 463. An image plane 466provided by ultrasound imaging probe 456, a HIFU beam 468 provided byHIFU therapy probe 452, and a focal point 464 can be visualized in image463. An optional message 470 informs the clinician that the probes arenot properly aligned, which is apparent because imaging plane 466 andbeam 468 do not overlap, and further, focal point 464 does not liewithin image plane 466. While monitoring display 460 and image 463, theclinician can change the relative positions of ultrasound imaging probe456 and HIFU therapy probe 452, until focal point 464 lies withinimaging plane 466.

It should be noted image 463 is a two dimensional image, and those ofordinary skill in the art will readily recognized that even if the HIFUbeam and the imaging plane overlap in two dimensions, they may notoverlap in three dimensions. When image 463 indicates that the imagingplane and the HIFU beam overlap, a clinician can view the ultrasoundimage provided by the ultrasound imaging probe, to determine whether ornot the focal point of the HIFU beam can actually be visualized in theultrasound image. If not, this provides an indication that the spatialrelationship and orientation between the imaging plane and the HIFU beamare not properly aligned, and the clinician can further manipulate therelative positions of the imaging probe and the HIFU therapy probe,until the focal point of the HIFU beam both overlaps the imaging planein image 463, and can be visualized in the ultrasound image provided bythe ultrasound imaging probe. It should also be understood that trackingsystem 454 can provide additional images from different perspectives (orimage 463 could be rotated by tracking system 454) to provide feedbackto a clinician indicating which direction the ultrasound imaging probeand/or the therapy probe need to be manipulated, so that the HIFU beamcan be visualized in the image provided by the ultrasound imaging probe.

System 450 offers several advantages, including ease-of-use, the abilityto visualize complex treatment strategies, and the ability to visualizecomplex tumor and anatomy geometries.

Another aspect of the concepts disclosed herein relates to exemplarytherapy probes, some of which are optimized for vaginal therapy. Theseexemplary probes include the use of an aluminum lens in one exemplaryembodiment, and a spoon shaped transducer array in another embodiment.

FIGS. 5 and 6 provide details regarding the distal end of a transvaginaltherapy probe 204, while FIGS. 7A-7F are photographs illustrating thefabrication of a working model of transvaginal therapy probe 204.Referring to FIG. 5, expandable member 244 is coupled to a housing 252using o-ring 264. In a working embodiment, housing 252 was implementedusing brass, and a groove was included in the housing to accommodateo-ring 264 (see also FIG. 7E). A fluid line 254 is used to selectivelyinflate and deflate expandable member 244 (see also FIGS. 7E and 7F). Analuminum lens 256 is attached to the distal end of housing 252. Asdiscussed in detail below, one embodiment of the present inventionincludes an aluminum lens that is used to focus a HIFU beam in thevaginal environment.

FIG. 6 illustrates a cross-sectional view of a distal end oftransvaginal therapy probe 204. The HIFU transducer is implemented usinga PZT-8 crystal 258, which is securely bonded to aluminum lens 256. FIG.7A is a photograph of crystal 258 and aluminum lens 256 before they arebonded together. The crystal utilized in a working model is a flat,circular disk piezoceramic crystal (APC 880™, from AmericanPiezoceramics, Duck Run, Pa.), with dimensions of about 25.4 mm indiameter and 0.59 mm in thickness (corresponding to half wavelength ofAPC 880 at 3.5 MHz). In the working prototype, the crystal was adheredto the aluminum lens with a thin layer (approximately 0.025 mm) of epoxy(Hysol RE2039™ and HD3561™, available from Loctite Corporation, RockyHill, Conn.). The bonding surfaces were roughened with a fiberglassbrush and cleaned with acetone in an ultrasonic cleaner to ensureoptimal bonding conditions. A custom built plastic (Delrin™) fixture andmolds made of silicone rubber (RTV 630 A™ and RTV 630 ™ B, 10:1 by mass,available from GE Silicones, Waterford, N.Y.) ensured concentricalignment of the crystal and the lens during bonding. The crystal andlens were bonded under pressure (approximately 400 kPa), and the epoxywas allowed to set at a temperature of 150° C. for 3 hours.

The main elongate body of the working model of transvaginal therapyprobe 204 was implemented using a 9.52 mm (⅜″) outer diameter hollowaluminum tube 266 (see also FIGS. 7E and 7F). Tube 266 was adhesivelycoupled (using Threadlocker 271™ adhesive, from Loctite Corporation,Rocky Hill, Conn.) to the brass housing (i.e., housing 252). A flexiblecoaxial cable 268 (RG-58 coaxial cable), approximately 10 cm longer thanaluminum tube 266, was fed through the handle and its ground braidingwas attached to the inside of the brass housing with a screw 262 for aground connection (see FIG. 7B, in particular). To prevent electricalshorting, the inside of the brass housing, the braiding, and the screwwere coated with epoxy, which provided isolation relative to the exposedcoaxial cable center. The exposed coaxial cable at the end of the handlewas encased in plastic tubing (R3603, ½″ ID, from Saint-GorbainPerformance Plastics, Wayne, N.J.), and the tubing was secured to thehandle using a plastic tubing connector to protect the transducer fromwater exposure. A conductive O-ring 260 (FIG. 7D) was cut from 0.25 mmthick gold foil and soldered onto the center of the coaxial cable andthe crystal to electrically couple to crystal 258 (note connector Ashown in FIGS. 7B and 7C). The completed transducer (i.e., the combinedlens 256/crystal 258 assembly) was placed into brass housing 252 andsecured with epoxy (Hysol RE2039™ and HD3561™, from Loctite Corporation,Rocky Hill, Conn.). The crystal was air backed to ensure both coolingand minimum energy loss through the back-side. FIG. 7F is a photographof the completed working model of transvaginal therapy probe 204.

As noted above, the purpose of using the tracking system discussed aboveto control the spatial orientation between a transvaginal therapy probeand a transabdominal imaging probe is to enable real-time, image-guidedHIFU therapy. However, when the HIFU source is in operation, the highpower levels saturate the ultrasound image probe receiver and circuitry,resulting in interference band patterns on the ultrasound image. Toensure that the image is interference-free where the focal point of theHIFU beam is to be visualized in the ultrasound image, the pulse gatingmethod described in a related U.S. Pat. No. 6,425,867 (entitled“Noise-Free Real Time Ultrasonic Imaging of a Treatment Site UndergoingHigh Intensity Focused Ultrasound Therapy”), is used. As explained aboveand in this referenced patent, the HIFU source and the imagingultrasound source are synchronized so that the interference area,proportional to the duty cycle, is spatially stable and moveable, asschematically illustrated in FIGS. 1B and 1C. It has been empiricallydetermined that when the Sonosite C60 image probe is used in conjunctionwith transvaginal therapy probe 204, a 50% HIFU duty cycle is adequatefor visualization of the HIFU focal point, resulting in a 65-70 degreewindow of visualization (out of a total ultrasound imaging window of 135degrees), as shown in FIGS. 8A and 8B. An ultrasound image 270 in FIG.8A includes a 67 degree window 272 of visualization that is noise free.Note that window 272 is disposed about 10 degrees from the left edge ofthe image, so that noise 274 a obscures the first 10 degrees ofultrasound image 270, and noise 274 b similarly obscures the last 58degrees. An ultrasound image 276 in FIG. 8B also includes a 67 degreewindow of visualization that is noise free (i.e., a window 278). Notethat window 278 is shifted relative to noise free window 272 of FIG. 8A.Thus, in FIG. 8B, window 278 is disposed about 40 degrees from the leftedge, so that noise 280 a obscures the first 40 degrees of ultrasoundimage 276, and noise 280 b similarly obscures the last 28 degrees.Accordingly, the window of visualization can be shifted to ensure thatthe focal point of the HIFU beam can be visualized in the noise freeportion of the ultrasound image. It should be understood that the windowof visualization is dependent upon the image probe used and the imagingframe rate, and thus, other transabdominal imaging probes (or otherframe rates) might result in a larger or smaller window ofvisualization.

FIG. 9 is a block diagram 284 that illustrates the functional elementsused to empirically test the functionality of the concepts disclosedherein. The HIFU transducer incorporated into vaginal therapy probe 204was driven with an RF amplifier 286 (Model ENI A150™, from MKSinstruments, Andover, Mass.). A first waveform generator 294 (Model33120A™, from Agilent Technologies, Palo Alto, Calif.) was used toprovide the source signal. An RF power meter 288 (Model 4421™, BirdElectronics, Cleveland, Ohio) was connected between the amplifier and amatching network 290 to monitor electrical power output. A switch 292was coupled between the output of waveform generator 294 and RFamplifier 286, to serve as an on/off switch. A timer 296 connected tothe switch enabled HIFU exposure time to be measured. In order toprovide synchronization (i.e., to enable visualization of the focalpoint of the HIFU beam by shifting noise introduced into an ultrasonicimaging by the HIFU beam, as described above), a second waveformgenerator 298 and a computer 300 were utilized. Computer 300 employedLabView™ software (National Instruments of Austin, Tex.) to control bothwaveform generators via a GPIB (General Purpose Interface Bus)connection. Waveform generator 298 was used to generate an excitationpulse. The excitation pulse triggered the output of waveform generator298, which operated in burst mode, with a burst count corresponding to a50% duty cycle. To ensure that the interference bands were spatiallystable, the excitation pulse must always fall on the same image probearray element. The excitation pulse frequency (EPF) varied with imagingdepth and was determined experimentally (by changing the EPF until theinterference bands were spatially stable) and was then entered manuallyinto the LabView™ control program. As described above, a tracking system(or a frame 200) can be used to ensure that the spatial orientationbetween transabdominal imaging probe 202 and transvaginal therapy probe204 remains constant once it has been adjusted so that the focal pointof the HIFU beam generated by transvaginal therapy probe 204 lies withinthe imaging plane generated by transabdominal imaging probe 202. Theultrasound image generated by transabdominal imaging probe 202 is viewedon a display 302.

Development of HIFU with Aluminum Lens

A study of the female pelvic anatomy was performed to determine theoptimal geometry and dimensions for transvaginal therapy probe 204 and aframe which mechanically coupled the therapy transducer to an externalimaging probe. Images from the Visible Human Project (National Libraryof Medicine, National Institute of Health), Gray's anatomy, 18 pelvicultrasounds, and fibroid patient data files were used. Variousconfigurations of transvaginal therapy probes and frames were modeledwith SolidWorks™ (SolidWorks Corporation, Concord, Mass.) designsoftware to determine optimal component sizes and geometry based on theabove noted anatomical study.

The anatomical study revealed vaginal lengths ranging from 6-11 cm,uterine lengths of 5-9 cm, and uterine widths of 2-5 cm. A transvaginaltherapy probe in accord with the present invention was designed to treatfibroids along the uterine cavity while placed in the vaginal fornixsurrounding the cervix. Therefore, a HIFU focal length of 4 cm wasdetermined to be optimal.

Numerical simulations indicated that an aluminum lens would be effectivein focusing ultrasound energy. It was determined that a flat crystal andlens design (versus a spherical shell) would be used due to crystalavailability, cost, and the possibility of using various lens geometriesand focal configurations in the future. Aluminum has a low acoustic lossand a low characteristic acoustic impedance (ZA_(Al)=17.3 Mrayls)relative to most metals (Z_(stee1)=46.7 Mrayls, Z_(copper)=42.5 Mrayls,and Z_(titanium)=27.0 Mrayls), making aluminum a suitable material foran acoustic lens in terms of minimizing attenuation and acting as anacoustic matching layer. Due to the high acoustic velocity of aluminum(6363 m/s) compared to water (1483 m/s), the curvature of the lens wassmall, and the maximum thickness of the lens was only 3 mm.

Based on the desired focal length and calculated attenuation losses inuterine tissue and fibroids, a PZT-8 crystal, 2.54 cm in diameter with anominal frequency of 3.5 MHz, was selected to provide a sufficient focalgain. A 2.54 cm aluminum lens with a 4 cm focal length resulted in amaximum lens thickness at the outer edge of 3 mm and an f-number of1.57. Although side lobes were noticed in the Schlieren imaging, theywere quantified as relatively small (approximately 20 dB) compared topeak focal intensities on the field map. Such side lobes may be a resultof re-radiation, reflections, and shear wave conversion within the lensand at the crystal-epoxy-lens interface, since they were apparent inanother HIFU transducer design at similar power levels, which alsoinvolved the use of a PZT crystal bonded to an aluminum waveguide.Although the epoxy used to bond the aluminum lens to the PZT wasnonconductive, roughness on both lens and PZT surfaces at themicroscopic level allowed for areas of direct contact and thus,conduction while the two surfaces were bonded under 400 kPa of bondingpressure.

The maximum diameter of the brass housing for the PZT crystal andaluminum lens combination was 28.5 mm, which is sufficiently small toreadily fit into the vagina. While optimizing the HIFU transducer sizeto fit in the vagina, it was ensured that the aperture size chosen wasable to deliver sufficient power to the treatment site. A transvaginalversus transabdominal treatment approach was chosen since it providedthe shortest acoustic path to the uterus (approximately 0.5 cm from thevaginal fornix to the uterus, versus approximately 4 cm via the abdomen,depending on bladder size). The large attenuation loss associated withthe abdominal path (losses in skin, fat, abdominal wall, and bladderfluid) were thus eliminated using the transvaginal approach.

As noted above, a piezoelectric ceramic (PZT-8) crystal was selected togenerate the HIFU, and an aluminum lens was selected to focus the HIFUbeam. The curvature of the aluminum lens was calculated such that wavesfrom each point on the surface of the crystal would pass through thelens and arrive at the focus at the same time. This focusing effect isschematically illustrated in FIG. 10A, for a lens focusing at 4 cm,where t_(1i)+t_(2i)=t₀ and i represents a point location on the crystal.The variables used in Equation 1 (below) that govern the shape of thelens are indicated in FIG. 10A. The coordinates of the lens curvaturefit the quadratic relation in Equation (1), where (x_(i), y_(i)) are thecoordinates of the lens curvature, x_(f) is the focal length, and c₁ andc₂ are the measured acoustic velocities in the aluminum lens (6363 m/s)and in water (1483 m/s), respectively:

$\begin{matrix}{{{x_{i}^{2}( {1 - \frac{c_{2}^{2}}{c_{1}^{2}}} )} + {x_{i}( {{2x_{f}\frac{c_{2}}{c_{1}}} - {2x_{f}}} )} + ( y_{i}^{2} )} = 0} & (1)\end{matrix}$

A computer simulation was used to determine the effectiveness of thealuminum lens in focusing ultrasound. Wave 2000 Pro™ (Cyberlogic, NewYork, N.Y.), a program for studying two-dimensional (2D) wavepropagation fields, was used to compute the finite difference solutionto the 2D wave equation in both spatial and temporal domains. Shear andcompression coupling and viscous loss attenuation were included in thealgorithm. The geometry, material properties, and ultrasound sources andreceivers were modeled. The geometry, shown in FIG. 10B, consisted of asimplified model of the transducer: an air-backed PZT-8 crystal bondedto an aluminum lens with an epoxy bond layer. Source pulses of 3 ms andcontinuous wave sources were modeled in a simulated treatment pathconsisting of water and uterine tissue. Simulated ultrasound pointreceivers for particle displacement measurement were located at thefocus and at various points along the focal axes (1, 2, 5, 10, and 20 mmto the left and right of the focus, and 1, 2, and 5 mm above and belowthe focus), as depicted in FIG. 10B. The time duration for eachsimulation was set at 45 ms, allowing the wave to propagate a fewcentimeters past the focus. Normalized particle displacement data wereextracted from the simulations. An aluminum lens developed using theabove described model was machined using a CNC lathe. Fabrication of thetransvaginal therapy probe is described above.

Wave 2000 Pro™ computer simulations demonstrated the feasibility of thealuminum lens design in focusing ultrasound. A propagating 3 ms pulsefor a 3.5 MHz sinusoidal ultrasound source focusing at 4 cm through analuminum lens at various times was simulated. The normalized peakparticle displacement amplitudes determined from simulation receiverdata at various locations were also calculated. FIG. 11A is a compositeof images extracted from the Wave 2000 Pro™ simulation, showing a 3.5MHz, 3 μs sinusoidal pulse wave at four different times (7 μs, 2 μs, 30μs, and 37 μs). The approximate time when the wave front reached thefocus was at 30 μs. The program created a black background during thesimulation for contrast, and the various minima and maxima of the waveare shown in white, with areas that remain black showing locations wherethe waveform has zero amplitude.

FIG. 11B graphically illustrates the peak normalized particledisplacements collected from the Wave 2000 Pro™ simulation receiverdata. Since acoustic pressures are proportional to particledisplacements, the half-pressure maximum focal dimensions can beestimated as being about 10 mm in length by about 1 mm in width, asindicated in FIG. 11B.

The actual acoustic beam pattern provided by the aluminum lens and PZT-8crystal fabricated as described above was initially determined with aSchlieren imaging system at three different acoustic power levels,including: 10, 30, and 60 W (continuous wave). FIG. 12A illustrates acomposite of the Schlieren images obtained at the above noted powerlevels. Side lobes 304 are indicated at power levels around 60 W.

FIG. 12B graphically illustrates an acoustic field map created usingdata collected with a PVDF needle hydrophone (from NTR Systems Inc.,Seattle, Wash.) during empirical testing of the transducer generatedusing the PZT-8 crystal and the aluminum lens described above.Technically, the act of transduction of energy (from electrical to aacoustical) is performed by the crystal, however, those of ordinaryskill in the art will readily recognize that the term transducer isoften used to refer not only to the crystal itself, but also to acrystal combined with a lens. The hydrophone was 0.5 mm in diameter andwas moved using stepper motors. The acoustic power output was determinedusing a radiation force balance technique. The field map shows the HIFUfocus at a half-pressure maximum (26 dB) with measured dimensions ofabout 11 mm in length and about 1.2 mm in width, which are similar tothe values predicted with the computer model. Side lobes can be seen butwere at values below approximately 20 dB. The acoustic power output wasdetermined using a radiation force balance technique.

Results obtained from the radiation force balance are shown in FIG. 13.This plot shows the correlation between electrical power and acousticpower, as well as the efficiency at the power levels tested. The averageefficiency between 0 and 150 W of acoustic power was determined to be58%, +/−2% (n=9 power levels).

In-vitro testing of the PZT-8/aluminum lens transducer in gel and animaltissue verified the functionality of the design. A transparenttissue-mimicking gel phantom was used to determine if lesions can beformed at target locations, if these lesions can be visualized usingultrasound, and if the water balloon affects the formation of lesions.The thermally sensitive gel employed was based on a combination ofbovine serum albumin and polyacrylamide, and changes from transparent toopaque when treated with HIFU. The attenuation of the gel was measuredto be 0.012+/−0.002 NP/cm/MHz (n=30). Gel blocks (6.5×5.5×5.5 cm) wereplaced in a plastic holder, submerged, and anchored in a plastic tankfilled with degassed distilled water at room temperature. Thetransvaginal therapy probe described above (i.e., transvaginal therapyprobe 204) was suspended in the water tank using a metal clamp andpositioned such that the focal region of the HIFU transducer was withinthe gel block, and the image probe was capable of visualizing thetreatment.

Three treatment scenarios were investigated, as follows: (1) thetransducer was placed directly on the gel surface; (2) the transducerwas placed 1.2 cm away from the gel surface and separated therefrom by awater-filled condom; and, (3) the transducer was placed 1.2 cm away fromthe gel surface without a water-filled condom intervening. All lesionswere produced using 46 W of acoustic power for 5 seconds at 50% dutycycle. The ultrasound imaging unit (Sonosite™, from Sonosite Inc.,Bothell, Wash.) was connected to a digital video recorder and ultrasoundimages were recorded during treatment. A digital camera, mounted on atripod, was used to photograph lesions formed in the transparent gel.Lesion dimensions were measured using these photographs within AdobePhotoshop™ (Adobe Systems Incorporated, Seattle, Wash.).

TABLE I Measured dimensions for HIFU lesions in gel with and withoutwater stand-off. Treatment scenario In situ focal Lesion Lesion (n = 10intensity length width Ultrasound for each) (W/cm²) (mm) (mm)visualization Transducer 1410 11.2 +/− 0.8 2.2 +/− 0.6 10/10 directly ongel 1.2 cm 1590 13.5 +/− 1.1 2.6 +/− 0.7 10/10 separation; no condom 1.2cm  1590¹ 13.3 +/− 0.9 2.5 +/− 0.8 10/10 separation; with condom¹Attenuation of the 0.07 mm thin condom (Trojan Brand Non-Lubricated,CWI Carter Products Div., New York, NY) was assumed to be zero.

FIG. 14A illustrates a composite image including both a photograph 320of the distal end of transvaginal therapy probe 204 coupled to a gelphantom, as well as an ultrasound image 322 of the distal end oftransvaginal therapy probe 204 coupled to the gel phantom. In both thephotograph and the ultrasound image, brass housing 252, expandablemember 244, and aluminum lens 256 can be observed. Note that inultrasound image 322, degassed water 244 a used to inflate the latexcondom (i.e., expandable member 244) can be identified. FIG. 14B is acomposite image including a similar photograph and ultrasound image,taken after HIFU therapy. A lesion 326 can be observed in both aphotograph 324 and in an ultrasound image 328. These images depict atreatment scenario wherein the transducer and gel are separated by 1.2cm of water contained within a water-filled condom. The HIFU transducerand the water-filled condom are clearly seen in the ultrasound images(i.e., ultrasound images 322 and 328). Lesion 326, which was formed byHIFU, can be clearly seen in photograph 324 as a white opaque spot inthe transparent gel, and as a bright hyperechoic spot in ultrasoundimage 328. The lesion appears to be tadpole-shaped, indicative of thepresence of cavitation mechanisms during lesion formation. The measuredlesion dimensions for three different treatment scenarios (no condom/noseparation, 1.2 cm separation with no condom, and 1.2 cm separation withliquid-filled condom), are shown in Table I. At 46 W of acoustic powerand 50% duty cycle, the focal intensity was 1400 W/cm² with thetransducer on the surface of the gel and 1590 W/cm² with the transducerand gel separated by 1.2 cm of water. A two-sample, two-tailed testindicated no statistically significant difference between lesionscreated both with the water-filled condom stand-off, and without(P<0.05). Lesion size was proportional to HIFU focal intensity. Alllesions were visualized with ultrasound.

The ability for the device to produce and visualize lesions in tissuewas then determined using fresh turkey breasts. The turkey breastsamples used in the experiment were stabilized at 25° C. prior totreatment and had a measured attenuation of 0.096+/−0.002 NP/cm/MHz.Attempts were made to create lesions perpendicular to the muscle fibersat selected HIFU focal intensities between 500 and 4000 W/cm², at 5 and10 seconds of exposure, and 50% duty cycle. The spatial and temporalaveraged frequency dependent HIFU focal intensity ISATA was determinedto be:

$\begin{matrix}{I_{SATA} = {\frac{P_{A}*{DC}}{A}( {\mathbb{e}}^{{- 2}\alpha_{T}x_{T}} )( {\mathbb{e}}^{{- 2}\alpha_{w}x_{w}} )}} & (2)\end{matrix}$where P_(A) is acoustic power, DC is duty cycle, A is the half pressuremaximum (23 dB) focal area, α_(T) and α_(W) are the respectiveattenuation coefficients of tissue and water, and x_(T) and x_(W) arethe depths in tissue and water, respectively. The tissue was dissectedat the lesion location and lesion length and width were measured usingdigital calipers. It was noted whether or not each lesion was visualizedusing ultrasound imaging during treatment.

Such HIFU created lesions, and the ultrasound visualization of treatmentin a turkey breast using transvaginal therapy probe 204 are shown inFIGS. 15A and 15B. FIG. 15A is a photograph 330 of a dissected turkeybreast, which includes lesions induced by HIFU therapy. A lesion 332 awas generated using a power level of 3800 W/cm² applied for 5 seconds; alesion 332 b was generated using a power level of 1600 W/cm² applied for10 seconds; a lesion 332 c was generated using a power level of 2200W/cm² applied for 5 seconds; and a lesion 332 d was generated using apower level of 800 W/cm² applied for 10 seconds. Normal turkey breast(i.e., no lesions) is generally indicated by an arrow 334.

FIG. 15B is a composite image of a turkey breast and a HIFU therapyprobe, including an ultrasound image 336 a, generated before theapplication of the HIFU beam, and an ultrasound image 336 b, generatedafter the application of the HIFU beam. Each ultrasound image includes aturkey breast 335 and the distal portion of transvaginal therapy probe204, including aluminum lens 256. A lesion 338 is clearly visible afterthe HIFU therapy in ultrasound image 336 b.

As indicated below in Table II, visualization was successfully achieved100% of the time at a power level of 3600 W/cm², and 70% of the time ata power level of 1200 W/cm².

TABLE II Measured dimensions for HIFU lesions in a turkey breast at twointensity levels. In situ focal Lesion Lesion intensity length widthNumber of Ultrasound (W/cm²) (mm) (mm) samples visualization 1200 10.6+/− 3.1 2.1 +/− 0.3 10  7/10 3600 21.6 +/− 1.1 5.1 +/− 0.3 10 10/10

Once the effectiveness of transvaginal therapy probe 204 was empiricallytested using gel phantoms and turkey breasts as described above, theergonomics of transvaginal therapy probe 204, the frame, andtransabdominal imaging probe 202 were tested in six healthy humanvolunteers, in accordance with a human subjects research protocolapproved at the University of Washington. The volunteers were neitherpregnant nor had undergone a hysterectomy. A sterile condom (toimplement expandable member 244) was secured to the distal end oftransvaginal therapy probe 204, lubricated, and filled with water priorto insertion into the vagina. Once the transvaginal therapy probe wasinside the vagina, the transabdominal imaging probe was positioned tovisualize pelvic structures and the transvaginal therapy probe. Uterusdimensions were measured on the ultrasound image. Once visualization waspossible, the transvaginal therapy probe was mechanically moved andpositioned to hypothetically treat various areas of the uterus. Theamount of transducer movement was quantified using a ruler drawn ontothe transvaginal therapy probe and by observing the relative position ofthe transvaginal therapy probe in the ultrasound image. The distancesfrom the transducer in the transvaginal therapy probe to the fundus,mid-uterus, and cervix were measured to determine the potentialtreatable area. Water was injected and removed from the condom todetermine the feasibility of using a water-filled condom as a stand-off.

TABLE III Human volunteer statistics and uterus measurements. BodyUterus Uterus Distance to Distance to Distance Age mass Uterus lengthwidth cervix^(e) mid uterus to Volunteer (years) index orientation^(d)(cm) (cm) (cm) (cm) fundus 1 26 20.4 A 6.15 3.42 1.88 2.69 3.92 2 2722.0 A 5.90 3.21 1.83 2.52 3.87  3^(a) 49 22.9 A 8.49 4.63 1.92 3.184.33 4 23 22.7 A 7.21 3.90 1.98 3.21 3.00 5 32 29.9 M 7.26 3.33 2.173.50 4.78  6^(b) 42 24.6 M 11.7 8.03 3.61 5.64 5.44 Mean 33.17 23.757.79 4.42 2.23 3.46 4.22 St Dev^(c) 12.23 3.31 2.13 1.84 0.69 1.13 0.84^(a)Volunteer had children. ^(b)Volunteer had a fibroid located in thefundus. ^(c)Standard deviation. ^(d)A = aniflexed; M = midline^(e)Distance measure from the aluminum lens of the transvaginal therapyprobe.

Volunteer statistics and uteri measurements are shown in Table III. Thevolunteers ranged in age between 23 and 49 years, and in body mass index(weight in kilograms divided by the square of height in meters) between20.4 and 29.9. One volunteer had previously given birth, and onevolunteer had a fibroid located in the fundus. Four volunteers hadaniflexed uteri (a condition in which the uterus is pointed towards theabdomen) and two had midline uteri. Uteri length ranged between 5.90 and8.49 cm and width ranged between 3.21 and 4.63 cm, excluding thevolunteer with a fibroid, wherein the total uterus length and width,including the fibroid, were 11.7 cm and 8.03 cm, respectively. As shownin Table III, if treatment was to be administered, the 4 cm focal lengthof transvaginal therapy probe 204 would have been sufficient to treatfibroids located in the cervix and mid-uterus of all volunteers (anaverage distance of 2.23 cm and 3.46 cm, respectively).

According to the survey completed by the volunteers after the study,entrance into the vagina was comfortable if lubrication was used andsufficient water was inside the condom to act as a cushion between thevaginal wall and the HIFU transducer (i.e., the distal end oftransvaginal therapy probe 204). No discomfort was experienced while theprobe was in the vagina and while the probe was being removed from thevagina.

The above-noted study provides a feasibility assessment for image guidedHIFU therapy using transvaginal therapy probe 204, transabdominalimaging probe 202, and a frame (or the free hand registration systemdiscussed above), for treating uterine fibroid tumors. The transvaginalHIFU transducer (crystal 258 and lens 256) has the potential to treatfibroids through the width of the uterus when placed in the vaginalfornix. In designing transvaginal therapy probe 204 and frames,anatomical constraints of the female pelvic structures were taken intoaccount. The 28.5 mm diameter transducer head was sufficiently small tofit into the vagina. While optimizing the HIFU transducer size to fit inthe vagina, it was ensured that the aperture size chosen was able todeliver sufficient power to the treatment site. Placement of the devicein human volunteers demonstrated successful visualization of the HIFUtransducer and the uterus. The water-filled condom and the transducerlens surface were easily seen in the ultrasound images. Since thetransducer had a fixed focal length of 4 cm, a potential treatmentlocation can be determined on the ultrasound image at a distance of 4 cmaway from the transducer lens. Mechanical movement of the HIFUtransducer was possible once in the vagina and provided access to apotential treatment area that spanned from the cervix to the fundus ofthe uterus. The ergonomic study indicated that the insertion,maneuvering, and removal of the probe were comfortable for thevolunteers. The ergonomic study also indicated that a HIFU transducerwith a fixed focal length of 4 cm is capable of treating fibroidslocated in the cervix and mid-uterus area in most women with aniflexedand midline uteri. However, fibroids located in the fundus of midlineuteri and uteri of women who have previously given birth (i.e., withinlarger uteri) may require a longer focal length or treatment usingtransabdominal HIFU. Since an individual lesion is not large enough tocover a fibroid, multiple lesions would be required for fibroidtreatment. Therefore, large fibroids may require a long treatment timeor not be suitable for HIFU treatment. The target fibroids for thistreatment modality are submucosal fibroids. Submucosal fibroids arelocated under the endometrium of the uterus, accessible with a 4 cmfocal length, and represent the most symptomatic type of fibroids. Theyare often smaller in size than intramural or subserosal fibroids, makingthem more suitable for HIFU treatment.

The two methods currently used for HIFU therapy visualization aremagnetic resonance imaging (MRI) and ultrasound. Both can be used toimage fibroids. In an ultrasound image, fibroids often appear hypoechoic(as darkened regions). The Sonosite™ ultrasound unit was chosen for thisstudy, since it allowed for image guidance and was portable andinexpensive compared to larger ultrasound units and MRI. As shown inthis study, transabdominal ultrasound image-guidance provides real-timeimaging of the HIFU treatment. MRI provides imaging visualization of theHIFU thermal field and coagulated region within five seconds oftreatment, and is thus not a real-time visualization. With ultrasoundimaging, treating tumors with multiple lesions is facilitated, since theHIFU-induced hyperechoic spot remains after treatment for a durationdependent on the exposure intensity. Furthermore, treatment dosimetry,and not just treatment location, can be determined, since thehyperechoic spot size is proportional to the size of the lesion created.It was noted in the turkey breast that hyperechoic spots only appearabove a specific intensity threshold (>1250 W/cm²). Therefore, there isa possibility that exposures at lower doses may result in a physicallesion that cannot be visualized. This apparent intensity threshold willneed to be determined in human uterus samples. The mechanisms behind theformation of hyperechoic spots are not well understood. However, it canbe inferred from the in vitro testing in this study that the hyperechoicregion during HIFU treatment is due to a combination of tissueproperties changing due to tissue necrosis, cavitation activity, andgross deformation resulting in voids within the tissue. It is desirableto determine the location of the potential area of lesion formationprior to treatment. An electronic method using position transducers fortargeting is currently being developed to enable the treatment area tobe visualized without relying on the hyperechoic spot. Furthermore,computer-aided treatments that keep track of the treated areas on theultrasound image may be employed in the future to compensate for anydecrease in echogenicity in the hyperechoic spot.

The in vitro testing in gel demonstrated the feasibility of using thetransvaginal HIFU transducer to form lesions. The testing on a turkeybreast indicated a HIFU dose dependent lesion formation in tissue. Itwas shown that increasing the intensity or exposure time can increaselesion size. It was also shown that the intensity required for the onsetof lesion formation was lower for a 10 second treatment duration (about760 W/cm²) versus a 5 second treatment duration (about 1170 W/cm²).Lower HIFU intensities (ranging from about 760 W/cm² to about 2800W/cm²) resulted in cigar-shaped lesions that have been characterized asdue to purely thermal effects. Higher HIFU intensities (i.e., aboveabout 2800 W/cm²) resulted in tadpole-shaped lesions, with a distincthead and tail that were characterized as lesions with a significantcontribution from inertial cavitation activity and vaporization.

The thermal and cavitation effects at the focus and surrounding tissuewill be subject to further investigation to determine optimal treatmentparameters for uterine fibroids. Effective acoustic coupling from theHIFU transducer to the tissue of interest is crucial for successfultreatment. Water is an effective acoustic coupler, due to its similarityin acoustic impedance to tissue. Since there was potential for air to betrapped between the transducer and the vaginal wall when the device wasused in vivo, a method of acoustic coupling was devised using awater-filled condom that eliminated pockets of air, as described infurther detail below. Testing of the device with the gel phantomrevealed that the condom essentially acted as an acousticallytransparent thin membrane that did not statistically affect the size oflesions. The condom further provided a sterile protective membrane.Focal depth control was possible by selectively inflating and deflatingthe condom with water and thus varying the distance between thetransducer and the uterus, effectively varying the treatment location.Water circulation within the condom provides cooling to the transducerwhile in operation. Factors such as blood perfusion, air entrapment, andnonlinear effects of HIFU treatment need to be taken into considerationand may be the subjects of a future investigation.

Still another aspect of the present invention is directed to a method ofverifying a quality of the coupling between an ultrasound therapy probeand a tissue interface. FIG. 17A schematically illustrates atransvaginal therapy probe 204 b coupled to a tissue mass 406.Transvaginal therapy probe 204 b is substantially similar totransvaginal therapy probe 204 described above, however transvaginaltherapy probe 204 b further includes a liquid flushing line 251, whosepurpose will be described in greater detail below. Transvaginal therapyprobe 204 b similarly includes housing 252 disposed at the distal end oftransvaginal therapy probe 204 b. Housing 252 encapsulates the therapytransducer. Expandable member 244 (i.e., a latex condom) is attached tohousing 252, and filled with liquid to facilitate coupling transvaginaltherapy probe 204 b to tissue mass 406. With respect to transvaginaltherapy probe 204 b, tissue mass 406 generally will be within theuterus. It should be understood that the method of verifying a qualityof the coupling between an ultrasound therapy probe and a tissueinterface is not limited to use with any specific therapy probe, or anyspecific tissue mass. Thus, the inclusion of transvaginal therapy probe204 b in FIG. 17A is intended to be exemplary, rather than limiting ofthe present invention.

A plurality of air bubbles 408 can be seen between expandable member 244and tissue mass 406. The presence of such air bubbles at the interfacebetween the therapy probe and the tissue mass will negatively affect thetransmission of the HIFU beam through the interface, which will resultin a degradation of the therapy being performed, because such airbubbles interfere with the propagation of the HIFU beam from the therapytransducer to the focal point/target area. The presence of air bubbleswill reduce the amount of energy transmitted by the HIFU beam. Generallysuch air bubbles are most likely to be outside of the expandable member,in between the expandable measure member and the tissue mass. The liquidused to inflate the expandable member is preferably treated to removeany air bubbles in the liquid (i.e. the liquid is degassed), so it ismore likely that air bubbles would become trapped outside of theexpandable member, as opposed to inside the expandable member. Todislodge air bubbles trapped between the expandable member and thetissue interface, transvaginal therapy probe 204 b can be manipulatedsuch that the expandable member moves relative to the tissue mass,thereby dislodging any air bubbles. An additional technique that can beused to dislodge air bubbles would be to inflate or deflate theexpandable member. Liquid flushing line 251 can be used to flush theinterface with a rinse liquid to remove the air bubbles, as indicated byan arrow 253. If the air bubbles have formed inside of the expandablemembrane, the liquid in the expandable membrane can be replaced withdegassed liquid. Examination of the positions of the air bubblesrelative to the interface and the expandable membrane will indicatewhether the air bubbles are located in the liquid filling the membrane,or between the membrane and the tissue, so an appropriate correctiveaction can be taken.

FIG. 16 shows a flowchart 390 that indicates the sequence of logicalsteps to determine whether such air bubbles are present. In a block 392a therapy probe is introduced into a body cavity, such as the vagina.While most often, therapy probes in accord with the present inventionwill be used within the body cavities, it should be understood thattherapy probes can also be used in external applications, so that thetherapy probe/tissue interface is outside the patient's body. Thus, itshould be understood that the present invention is not limited todetecting air bubbles at tissue interfaces within a body cavity. In ablock 394, the expandable member (such as a balloon or a latex condom)is inflated with a liquid (such as water or saline solution) thatsupports propagation of the HIFU beam. In some applications, theexpandable member may be at least partially inflated with the liquidbefore the therapy probe is introduced into a body cavity, to provide acushioning effect. In a block 395, the therapy probe is properlypositioned relative to the tissue interface, so that the expandablemember contacts the tissue interface and slightly deforms, therebyefficiently coupling the therapy probe to the tissue. In a block 396,the quality of the coupling between the expandable member and the tissueinterface is evaluated, to determine if there are any air bubbles withinthe liquid. In a decision block 398, it is determined whether any suchbubbles are present. If so, then in a block 400 appropriate action istaken to dislodge the air bubbles. Techniques for dislodging air bubblesinclude repositioning the therapy probe to dislodge the air bubbles,inflating or deflating the liquid-filled membrane to dislodge the airbubbles, and flushing the interface with an irrigation liquid todislodge the air bubbles. An additional check is then made to determinewhether any more air bubbles are present, after the therapy probe isrepositioned. If, in decision block 398, it is determined that no suchair bubbles are present, therapy is performed, as indicated in a block402.

FIG. 17B schematically illustrates transvaginal therapy probe 204 b,including expandable member 244, coupled to tissue mass 406, such thatno air bubbles are present at the tissue interface. Once administrationof the therapy is completed, the probe is removed from the body cavity,as indicated in a block 404 (of FIG. 16).

As noted in the details of block 396 (shown in FIG. 16), severaldifferent techniques can be used to check for the presence of airbubbles. A hysterscope can be used to optically check for the presenceof air bubbles, as indicated in a block 396 a. FIG. 18 is a photographof a commercially available hysterscope 416. Those of ordinary skill inthe art will recognize that a hysterscope is a relatively commongynecological instrument. Due to its widespread availability, mostmedical offices treating gynecological disorders will have access tosuch an instrument. Due to the small size of the hysterscope, it isquite feasible for both a transvaginal therapy probe and a hysterscopeto be accommodated in the vaginal canal at the same time. Thehysterscope provides real-time images, and can be manipulated so thatthe clinician can visually check for the presence of any air bubbles atthe interface between the tissue mass and the therapy probe. If theclinician observes the presence of any air bubbles at thetissue/transvaginal therapy probe interface, the clinician canmanipulate the transvaginal therapy probe to dislodge any air bubblesthat were observed. While a rigid hysterscope is illustrated, it shouldbe understood that flexible hysterscopes, or other flexible imagingdevices, can be similarly employed for this purpose.

The therapy probe itself can also be used to check for the presence ofair bubbles, when the therapy probe is energized at a low-power level,as indicated in a block 396 b. When energized at a low-power level, theHIFU transducer transmits a low-power pulse. The reflected pulse isdetected and analyzed. Either a therapy probe or an imaging probe can beused to detect the reflected pulse. If the intensity of the reflectedpulse is higher than a predefined threshold level, it can be concludedthat there are air bubbles disposed at the interface, and those airbubbles are responsible for the reflected pulse. For specificapplications and equipment, the threshold level can be determinedempirically. Otherwise, a reasonable threshold level would be a 15-20%increase in a background level. The HIFU beam is energized at alow-power setting to check for air bubbles, which ensures that tissuenecrosis does not occur until a satisfactory coupling of the therapyprobe to the tissue mass has been achieved and the HIFU beam isenergized at a substantially higher intensity.

Still another technique for determining whether any air bubbles arepresent at the tissue/therapy probe interface involves using anultrasound imaging probe, as indicated in a block 396 c. The ultrasoundimaging probe can either be integrated onto the therapy probe, or aseparate ultrasound imaging probe can be employed. Any air bubblespresent at the tissue/therapy probe interface can be readily identified,because they will appear as bright spots in the ultrasound image. If anultrasound imaging probe is used to determine whether any air bubblesare present, the therapy probe does not need to be energized at allduring the check for air bubbles.

Another aspect of the present invention is directed to still anotherembodiment of a transvaginal therapy probe 410 that includes a generallyspoon-shaped therapy transducer 412, a schematic representation of whichis provided in FIG. 19A. FIG. 19B is a schematic representation of thedistal end of transvaginal therapy probe 410, clearly showing generallyspoon-shaped therapy transducer 412. FIG. 19C schematically illustratestransvaginal therapy probe 410 removably coupled to a commerciallyavailable transvaginal imaging probe 120, to enable visualization of thefocal point of the HIFU beam during therapy, generally as describedabove. As indicated in FIG. 19C, the distal end of hysterscope 416 isalso removably coupled to the transvaginal therapy probe and thetransvaginal imaging probe. A hook and loop fastener 414 is employed toremovably couple the elements together. Those of ordinary skill in theart will readily recognize that other types of fasteners or mountingsystem can be similarly employed to removably couple the elementstogether. As noted above, it should be understood that in addition tohysterscope 416, other imaging devices can be used, such as opticalfiber-based flexible scopes. The development of digital imaging devicesis producing increasingly smaller devices, and if sufficiently smalldigital imaging devices become available, digital imaging devices canalso be employed for this purpose.

FIG. 19D schematically illustrates generally spoon-shaped transducer 412included in transvaginal therapy probe 410, clearly showing theplurality of different emitter elements that are included therein.Generally spoon-shaped transducer 412 includes 11 discrete emitterelements, all equal in area, each element being separated from itsneighbors by 0.3 mm. Six of the emitter elements have complete annuli,and five emitter elements have truncated annuli. The overall transducerdimensions are about 35 mm×60 mm. Generally spoon-shaped transducer 412is magnetic resonance image (MRI) compatible, has a center frequency of3 MHz, a focal length of 3-6 cm, a geometric focus of 5 cm, and amaximum focal intensity of 3000 W/cm². Techniques for ensuring that atransducer is compatible with MRI are disclosed by Hynynen K, DarkazanliA, Schenck J F et al. MRI-guided noninvasive ultrasound surgery.Med.Phys., vol. 20, pp. 107-115, 1993.

Still another aspect of the present invention is directed to anintegration of a hysterscope (to optically determine whether air bubblesexist at a tissue interface), a transvaginal imaging probe, and atransvaginal therapy probe into a single compact instrument that iscapable of optically determining whether any air bubbles exist at theinstrument/tissue interface, and which enables visualization of thefocal point of the HIFU beam during therapy. In a related embodiment, anoptical imaging element is incorporated into a transvaginal therapyprobe. Such an imaging element can be based on a hysterscope, asdescribed above, or based on an optical fiber, as well as sufficientlycompact digital imaging electronics (i.e. the imaging components in adigital camera or a digital video camera). Thus, in reference to FIG.19C, it should be understood that reference number 416 could beimplemented using a rigid hysterscope, a flexible optical fiber, orcompact digital imaging electronics.

Although the concepts disclosed herein have been described in connectionwith the preferred form of practicing them and modifications thereto,those of ordinary skill in the art will understand that many othermodifications can be made thereto within the scope of the claims thatfollow. Accordingly, it is not intended that the scope of these conceptsin any way be limited by the above description, but instead bedetermined entirely by reference to the claims that follow.

1. A probe for administering ultrasound therapy to a treatment sitewithin a patient's body, wherein a tissue mass is disposed between theprobe and the treatment site, the probe comprising: an elongatesupporting structure, having a distal end and a proximal end, whereinthe elongate supporting structure comprises a section at the proximalcud configured to be grasped and manipulated by a clinician to at leastinitially position the distal end of the elongate supporting structureat a desired location generally adjacent to the tissue mass; a highintensity focused ultrasound (HIFU) transducer disposed at the distalend of the elongate supporting structure, wherein the HIFU transducercomprises an aperture through which HIFU waves are transmitted, theaperture being of a sufficient size to transmit therapeutic HIFU wavessuch that the therapeutic HIFU waves have sufficient intensity remainingupon reaching the treatment site after being attenuated by the passageof the therapeutic HIFU waves through the tissue mass to achieve adesired therapeutic effect without substantially damaging a portion ofthe tissue mass through which the therapeutic HIFU waves initiallypropagate toward the treatment site; a light based imaging elementdirected generally toward an interface between as flexible membranesubstantially encapsulating the distal end of the elongate supportingstructure and the tissue mass, the light based imaging element beingconfigured to determine whether air bubbles are present at theinterface, wherein the flexible membrane is configured to be inflatedwith a liquid to as desired extent when the distal end of the elongatesupporting structure is disposed adjacent to the tissue mass such thatthe flexible membrane will substantially conform to the tissue mass and,thereby ultrasonically couple the HIFU transducer to the tissue mass andmeans for dislodging air bubbles at the interface.
 2. The probe of claim1 wherein the imaging element comprises an optical imaging element. 3.The probe of claim 2 wherein the optical imaging element comprises anoptical fiber.
 4. The probe of claim 1 wherein the imaging elementcomprises a digital imaging device.
 5. The probe of claim 1 wherein theHIFU transducer comprises an air backed piezoceramic crystal coupled toan aluminum lens element.
 6. The probe of claim 1 wherein the HIFUtransducer comprises a generally spooned-shaped transducer including aplurality of discrete emitter elements, each emitter element having asubstantially equivalent area.
 7. The probe of claim 1 wherein the meansfor dislodging air bubbles at the interface comprises a liquid flushline configured to discharge an irrigation liquid proximate the distalend of the elongate supporting structure to dislodge air bubblesproximate the distal end of the elongate supporting structure that couldinterfere with the HIFU waves transmitted by the HIFU transducer.
 8. Theprobe of claim 1 wherein the means for dislodging air bubbles comprisesa fluid line in communication with the interface between the flexiblemembrane and the distal end of the elongate supporting structure thefluid line being configured to selectively inflate and/or deflate theflexible membrane with the liquid.
 9. The probe of claim 1 wherein themeans for dislodging air bubbles comprises means for dislodging airbubbles at the interface between the flexible membrane and the tissuemass.
 10. A probe for administering ultrasound therapy to a treatmentsite within a patient's body, wherein a tissue mass is disposed betweenthe probe and the treatment site, the probe comprising: (a) an elongatesupporting structure having a distal end and a proximal end, wherein theelongate supporting structure comprises a section at the proximal endconfigured to be grasped and manipulated by a clinician to at leastinitially position the distal end of the elongate supporting structureat a desired location generally adjacent to the tissue mass; (b) a highintensity focused ultrasound (HIFU) transducer disposed at the distalend of the elongate supporting structure, wherein the HIFU transducercomprises an aperture through which HIFU waves are transmitted, theaperture being of a sufficient size to transmit therapeutic HIFU wavessuch that the therapeutic HIFU waves have sufficient intensity remainingupon reaching the treatment site after being attenuated by their passagethrough the tissue mass to achieve a desired therapeutic effect withoutsubstantially damaging a portion of the tissue mass through which thetherapeutic HIFU waves initially propagate toward the treatment site,the HIFU transducer further comprising at least one of the following anair backed piezoceramic crystal coupled to an aluminum lens element, ora generally spooned-shaped transducer comprising a plurality of discreteemitter elements, each emitter element having a substantially equivalentarea; and (c) means for dislodging air bubbles between the HIFUtransducer and the tissue mass.
 11. The probe of claim 10, furthercomprising a light based imaging element directed generally toward aninterface between a flexible membrane substantially encapsulating thedistal end of the elongate supporting structure and the tissue mass todetermine whether air bubbles are present at the interface, wherein theflexible membrane is configured to be inflated with a liquid to adesired extent when the distal end of the elongate supporting structureis disposed adjacent to the tissue mass such that the flexible membranewill substantially conform to the tissue mass and thereby ultrasonicallycouple the HIFU transducer to the tissue mass.
 12. The probe of claim 10wherein the imaging element comprises an optical fiber.
 13. The probe ofclaim 10 wherein the imaging element comprises a digital imaging device.14. The probe of claim 10, further comprising a hysterscope proximatethe distal end of the elongate support member, wherein the hysterscopeis configured to provide real-time images to visually check for thepresence of air bubbles between the HIFU transducer and the tissue mass.15. The probe of claim 10, further comprising means for emitting, anon-therapeutic level of ultrasound to detect air bubbles proximate thedistal end of the elongate supporting structure.
 16. The probe of claim15 wherein the means for emitting, the non-therapeutic level ofultrasound to detect air bubbles comprises the HIFU transducer.
 17. Theprobe of claim 10 wherein the means is dislodging air bubbles comprisesa flushing line configured to flush a rinse liquid proximate the distalend of the elongate supporting structure to dislodge air bubblesproximate the distal end of the elongate supporting structure.
 18. Therobe of claim 10 wherein the means for dislodging air bubbles comprisesa fluid line configured to inflate and/or deflate a flexible membraneover the distal end of the elongate supporting structure.